CN110960747B - High-precision analgesia pump and working method - Google Patents
High-precision analgesia pump and working method Download PDFInfo
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- CN110960747B CN110960747B CN201911317998.7A CN201911317998A CN110960747B CN 110960747 B CN110960747 B CN 110960747B CN 201911317998 A CN201911317998 A CN 201911317998A CN 110960747 B CN110960747 B CN 110960747B
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- 230000036592 analgesia Effects 0.000 title claims abstract description 18
- 238000000034 method Methods 0.000 title claims abstract description 17
- 229920001296 polysiloxane Polymers 0.000 claims abstract description 134
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims abstract description 82
- 238000001514 detection method Methods 0.000 claims abstract description 61
- 238000001802 infusion Methods 0.000 claims description 80
- 239000007788 liquid Substances 0.000 claims description 56
- 238000005070 sampling Methods 0.000 claims description 53
- 239000013307 optical fiber Substances 0.000 claims description 46
- 238000013016 damping Methods 0.000 claims description 42
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 claims description 36
- 239000000835 fiber Substances 0.000 claims description 28
- 230000008859 change Effects 0.000 claims description 24
- 229910052742 iron Inorganic materials 0.000 claims description 18
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 16
- 239000000741 silica gel Substances 0.000 claims description 16
- 229910002027 silica gel Inorganic materials 0.000 claims description 16
- 238000007789 sealing Methods 0.000 claims description 13
- 238000004891 communication Methods 0.000 claims description 10
- 230000001105 regulatory effect Effects 0.000 claims description 10
- 238000012546 transfer Methods 0.000 claims description 10
- 230000000202 analgesic effect Effects 0.000 claims description 7
- 239000000463 material Substances 0.000 claims description 3
- 238000004904 shortening Methods 0.000 claims description 3
- 230000005540 biological transmission Effects 0.000 claims 1
- 230000001276 controlling effect Effects 0.000 claims 1
- 230000033228 biological regulation Effects 0.000 abstract description 8
- 230000010412 perfusion Effects 0.000 abstract description 2
- 239000003814 drug Substances 0.000 description 18
- 230000033001 locomotion Effects 0.000 description 11
- 229920002379 silicone rubber Polymers 0.000 description 9
- 230000009467 reduction Effects 0.000 description 7
- 239000004945 silicone rubber Substances 0.000 description 6
- 239000012530 fluid Substances 0.000 description 5
- 230000035945 sensitivity Effects 0.000 description 5
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- 238000006243 chemical reaction Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000005611 electricity Effects 0.000 description 2
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- 238000012986 modification Methods 0.000 description 2
- 238000003199 nucleic acid amplification method Methods 0.000 description 2
- 239000008213 purified water Substances 0.000 description 2
- 238000003860 storage Methods 0.000 description 2
- 206010001526 Air embolism Diseases 0.000 description 1
- 230000002159 abnormal effect Effects 0.000 description 1
- 238000005299 abrasion Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16804—Flow controllers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/36—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests with means for eliminating or preventing injection or infusion of air into body
- A61M5/365—Air detectors
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/05—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using mechanical effects
- G01F1/34—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using mechanical effects by measuring pressure or differential pressure
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
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- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Anesthesiology (AREA)
- Animal Behavior & Ethology (AREA)
- Engineering & Computer Science (AREA)
- Vascular Medicine (AREA)
- Veterinary Medicine (AREA)
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- General Physics & Mathematics (AREA)
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Abstract
The utility model provides a high-precision analgesia pump and a working method, comprising a perfusion tube, a microcontroller, a water pump, a flow detection device and a flow regulation device, wherein the flow regulation device comprises a micro speed-reducing motor, a screw rod, a nut slider, a slide rod, a fixed fastener, a movable fastener, a first silicone tube, a silicone tube intermediate connector, a hollow round rod and a second silicone tube; the method can realize high-precision real-time adjustment of the analgesia pump, and avoids the influence of various external factors on flow adjustment.
Description
Technical Field
The disclosure relates to the technical field of analgesic pumps, in particular to a high-precision analgesic pump and a working method.
Background
The statements in this section merely provide background information related to the present disclosure and may not necessarily constitute prior art.
The disposable analgesia pump is a medical appliance which is commonly used in the medical field at present, and achieves the purposes of treatment and rapid analgesia mainly by intravenous administration of a patient.
The inventor of the present disclosure finds that (1) the actual injection speed of the existing disposable analgesic pump is affected by the type of the liquid medicine, the viscosity of the liquid medicine, and the temperature, and the physical properties of the elastic liquid storage device also cause the change of the injection speed (for example, the elasticity of the silica gel is large at the beginning, the flow speed is faster than the nominal flow speed), the precision of the flow limiting device (i.e., the flow regulating device) is low, and the disposable cost is relatively high; (2) the minimum detection flow value of the current flowmeter is large, the minimum flow detection value of the commonly used flowmeter in the market is about ten milliliters per hour, and the current analgesia pump is adjusted at 2ml per hour, namely the current flowmeter can not meet the flow detection requirement in the infusion process, so that the closed-loop control of the infusion volume can not be realized; (3) the conventional small flow regulating valve regulates the opening size of the valve by moving the valve core, and generates great flow change for a small movement stroke of small flow, namely the conventional small flow regulating valve can not meet the flow regulating requirement in the infusion process; (4) the prior bubble sensor can adopt ultrasonic detection and photoelectric detection, the ultrasonic detection cost is relatively high, the sensor and the infusion tube are required to be in close contact (the reflection on the surface of the tube and the acoustic impedance are reduced), the photoelectric detection structure is simple, the cost is low, the matching requirement of the infusion tube and the photoelectric detection device is low, the principle is that the light intensity change generated by bubbles is used for detection, but the photoelectric detection mode is easily influenced by the light transmittance of the infusion tube and the infused liquid (such as different liquid medicine transmittances), the light source change, dust, photosensitive elements, and other factors, at the same time, it is not easy to reduce the effect of the above factors by increasing the light intensity, because increasing the light intensity reduces the resolution of detecting bubbles (the sensitivity is low), i.e., are not conducive to the detection of small bubbles, and also may cause light contamination of some medical fluids, thereby limiting their practical use.
Disclosure of Invention
In order to overcome the defects in the prior art, the present disclosure provides a high-precision analgesia pump and a working method thereof, which can realize high-precision real-time regulation of the analgesia pump, and avoid the influence of various external factors on flow regulation.
In order to achieve the purpose, the following technical scheme is adopted in the disclosure:
the present disclosure provides, in a first aspect, a high precision analgesia pump.
A high-precision analgesia pump comprises a perfusion tube, a microcontroller, a water pump, a flow detection device and a flow adjusting device; the water pump is used for providing liquid with certain pressure to the flow detection device, and the flow detection device is used for detecting the flow of the liquid in real time and transmitting the flow to the microcontroller;
the flow regulating device comprises a miniature speed reducing motor, a screw rod, a nut slider, a sliding rod, a fixed clamping piece, a movable clamping piece, a first silicone tube, a silicone tube middle connecting piece, a hollow round rod and a second silicone tube, wherein one end of the first silicone tube is connected with the first silicone tube connecting piece, the first silicone tube connecting piece is fixed through the fixed clamping piece, the second silicone tube connecting piece is connected with the water outlet end of the sampling capillary tube through a waterway connecting pipe, one end of the hollow round rod is opened and penetrates through the first silicone tube connecting piece to be connected with the waterway connecting pipe, the other end of the hollow round rod is closed and penetrates through the second silicone tube to reach the silicone tube middle connecting piece, a liquid outlet hole is formed in the hollow round rod, and the outer diameter of the hollow round rod is smaller than the inner diameter of the first silicone tube;
the other end of the first silicone tube is connected with one end of a second silicone tube through a silicone tube middle connecting piece, the other end of the second silicone tube is connected with a second silicone rubber connecting piece, the silicone tube middle connecting piece is connected with a sliding rod through a hanging piece and can slide along the sliding rod, the second silicone tube connecting piece is fixedly connected with a movable clamping piece, the movable clamping piece is fixedly connected with a nut sliding block and can move along a screw rod and the sliding rod, the water outlet end of the second silicone rubber connecting piece is connected with a water pressure box, the infusion bag is arranged in the water pressure box, the water pressure box is filled with water, and the output port of the infusion bag is connected with an infusion tube;
the microcontroller controls the micro speed reducing motor to rotate the screw rod and move the nut slide block to drive the movable clamping piece in real time according to the detected transfusion flow value, further drives the first silica gel tube and the second silica gel tube to stretch and contract to enable the diameter and the length of the tubes to change, controls the extension of the silica gel tube to enable the flow resistance to increase and enable the flow rate to decrease when the flow rate is larger than a given value, otherwise controls the shortening of the silica gel tube to enable the flow resistance to decrease and enable the flow rate to increase and adjusts the stretching of the silica gel tube to enable the flow rate to be stabilized on the given value when the flow rate is smaller than the given value.
As some possible implementation manners, the first silicone tube and the second silicone tube are made of the same material, and the wall thickness of the second silicone tube is greater than that of the first silicone tube.
As some possible implementations, the water pump includes a water pump housing, a piston, and a spring, the piston and the water pump housing form a first chamber, the spring is fixedly connected to an end of the piston away from the first chamber, and the spring is in a compressed state.
As some possible implementation manners, the flow detection device comprises a sampling capillary tube and pressure sensors of the same type arranged at two ends of the sampling capillary tube, one end of the sampling capillary tube is connected with the water outlet end of the water pump, the pressure sensors are in communication connection with the microcontroller, and when liquid passes through the sampling capillary tube, the microcontroller performs infusion flow detection by using the pressure difference of the liquid at two ends of the sampling capillary tube according to the poisson's law.
As possible implementation manners, a damping iron rod is fixed on one side, far away from the slide rod, of the silicone tube middle connecting piece, and the silicone tube middle connecting piece further comprises a damping magnet opposite to the damping iron rod in position, the damping magnet is fixedly connected with a self-holding electromagnet, and the self-holding electromagnet controls the distance between the damping magnet and the damping iron rod according to instructions of a microcontroller so as to control the action of the silicone tube middle connecting piece.
As possible implementation manners, a magnet is fixed on the nut sliding block, a first hall limit switch and a second hall limit switch are arranged at a preset interval in the direction of the sliding rod, when the magnet is close to the first hall limit switch (or close to the second hall limit switch), the microcontroller controls the micro speed reduction motor to stop, and the limit switch is arranged to control the stroke of the nut sliding block to play a limiting protection role.
As some possible realization methods, be equipped with the optic fibre formula bubble sensor for detection on the position that is close to syringe needle port joint on the transfer line, optic fibre formula bubble sensor for detection is including setting up the many emission optic fibre that set up side by side along the transfer line direction of transfer line one side and setting up the receiving fiber relative with emission optic fibre at the transfer line opposite side, the light-emitting port and the relative setting of first photosensitive diode of receiving fiber, first photosensitive diode and microcontroller communication connection.
As a further limitation, the device further comprises a reference optical fiber type bubble sensor arranged behind the position of the detection optical fiber type bubble sensor on the infusion tube, the optical fiber arrangement in the reference optical fiber type bubble sensor is completely the same as that of the detection optical fiber type bubble sensor, the reference optical fiber type bubble sensor and the emission optical fiber in the detection optical fiber type bubble sensor share one light source, the emission optical fiber of the reference optical fiber type bubble sensor is arranged opposite to a second photosensitive diode, the second photosensitive diode is in communication connection with a microcontroller, and the microcontroller is used for judging whether bubbles are generated according to the contrast of the brightness degrees of the first photosensitive diode and the second photosensitive diode.
As possible implementation manners, the water pressure box comprises a water pressure box shell, a box cover is arranged at the top of the water pressure box, a box cover sealing ring is arranged on the box cover, the box cover is fixedly connected with the shell through a sealing buckle, an exhaust port is formed in the box cover, the exhaust port is controlled to be opened and closed through an exhaust valve, a convex water inlet and an infusion bag outer port are formed in the water pressure box shell, and the infusion bag outer port is sealed through an infusion bag outer outlet sealing ring.
The second aspect of the present disclosure provides a method of operating a high-precision analgesia pump.
When liquid flows in the sampling capillary tube, the pressure sensors at two ends of the sampling capillary tube convert corresponding pressure signals into electric signals and transmit the electric signals to the microcontroller, and the microcontroller obtains the flow Q of the liquid in the sampling capillary tube according to Poiseul's law as follows:
Q＝K(p2-p1)/η
wherein (p)2-p1) Is the pressure difference between two ends of the sampling capillary, eta is the viscosity coefficient of the liquid, K is the geometric constant of the sampling capillary, and K is pi R4And 8L, wherein R is the inner radius of the sampling capillary, L is the length of the sampling capillary, and pi is the circumferential ratio, the viscosity eta of the reference liquid is obtained by looking up the table, and the flow rate of the liquid flowing in the sampling capillary is further calculated.
As some possible realizations, the wall thickness of the second silicone tube is greater than that of the first silicone tube, and when the flow rate deviates from a given value, if the flow rate is larger than the set value, the microcontroller controls the nut slide block to move so that the first silicone tube and the second silicone tube extend to increase the flow resistance and reduce the flow rate, when the self-holding electromagnet is in a contraction state (the middle connecting piece of the silicone tube is not subjected to resistance), the change range of the diameter and the length of the first silicone tube is larger than that of the second silicone tube, the coarse flow regulation (mainly diameter regulation, the flow resistance is inversely proportional to the 4-order power of the equivalent diameter) is realized, when the self-holding electromagnet is in an extending state, the damping iron rod is in contact with the damping magnet, the stress of the middle connecting piece of the silicone tube is fixed under the damping action, the movement amount of the second silicone tube is larger than that of the first silicone rubber (even if the acting force of the first silicone tube is smaller than that of the second silicone tube). At the moment, the pipe diameter and the length of the second silicone tube are mainly adjusted (the length is mainly adjusted, and the flow resistance is in direct proportion to the length), so that the flow fine adjustment is realized. The range of coarse adjustment, i.e. adjustment, is larger, the fine adjustment, i.e. adjustment, can improve the precision (the flow resistance of the second silicone tube is much smaller than that of the first silicone tube), which is similar to the precision electronic instrument which usually adopts coarse adjustment and fine adjustment of the resistance to realize the fine adjustment (the adjustment of the micro flow regulator is that the flow resistance corresponds to the resistance).
As a further limitation, the microcontroller controls the damping iron rod to be in incomplete contact with the damping magnet and to have a certain gap, the damping iron rod can do certain damping movement along the damping magnet, and the flow regulation mainly based on fine adjustment is realized.
Compared with the prior art, the beneficial effect of this disclosure is:
1. the microcontroller controls the micro speed reduction motor to rotate the screw rod and move the nut slide block to drive the movable clamping piece in real time according to the detected infusion flow value, so that the diameter and the length of the tube are changed by driving the expansion of the first silicone tube and the second silicone tube, when the flow is larger than a given value, the extension of the silicone tube is controlled to increase the flow resistance and reduce the flow, otherwise, when the flow is smaller than the given value, the silicone tube is controlled to shorten the flow resistance and reduce the flow, the flow is stabilized on the given value by adjusting the expansion of the silicone tube, coarse flow adjustment and fine flow adjustment are realized through the matching of the first silicone tube and the second silicone tube, the control precision of the flow is greatly improved, and the influence of the type of liquid medicine, the viscosity of the liquid medicine, the temperature and the elastic liquid storage device on the flow adjustment is avoided.
2. The conventional small-flow regulating valve adjusts the size of an opening of the valve by moving the valve core, the small movement stroke (the change of a few tenths of millimeters) of the small flow can also generate large flow change, along with the reduction of the flow, the adjustable ratio of the valve can be reduced, and if the small movement stroke is difficult to adjust the flow, the flow can be adjusted by changing the flow resistance through stretching the silicone tube (the flow can be changed in more than twenty millimeters), the adjustable range is wide (the adjustable ratio is large), the structure is simple, the requirement on the machining and assembling precision is low, and the problem of abrasion does not exist.
3. The hydraulic pressure box is arranged, the flow of water is converted into the flow of liquid medicine, the flow is the same (the liquid is not compressible), and the liquid medicine is not mixed, so that the flow of the liquid medicine to be infused can be obtained by detecting the flow of the water, and the liquid medicine cannot be polluted. The precise infusion is realized by indirectly measuring water (purified water), and because the purified water flowing in the capillary tube and the regulator can not cause blockage (the blockage problem is larger for micro flow, because the pipe diameters of the sampling capillary tube and the regulator are very thin), the contradiction between the precise infusion and high cost is also solved (only an infusion bag and the infusion tube are replaced, and other parts are repeatedly used), therefore, the cost of the infusion pipeline is the same as that of a common disposable infusion device, the disposable use cost is not high, the disposable use cost is much lower than that of a conventional analgesia pump, and the economic burden of a patient is reduced; meanwhile, the compression spring and the piston are matched as power, and portable infusion can be realized.
4. The optical fiber type bubble sensor disclosed by the disclosure detects bubbles by utilizing the characteristic that the bubbles can cause the change of light intensity, and the sensitivity of the optical fiber type bubble sensor is very sensitive to the change of a light source and the like. The two photosensitive diodes are positioned in the same environment, the influence of temperature and dust is the same, the effect generated by the two photosensitive diodes can be basically offset, the two photosensitive diodes are only sensitive to the light intensity change caused by bubbles, and bubble signals and interference signals are identified by utilizing the characteristic that the bubbles move at a constant speed, so that the optical fiber type bubble transmitter has high sensitivity (good stability), a common brightness light emitting diode (low-brightness LED) can meet the requirement, and low brightness is also favorable for detecting small bubbles (the light intensity change caused by the small bubbles is small when the brightness is high).
5. The optical fiber type bubble sensor disclosed by the disclosure is arranged for multi-point detection, namely, the emission optical fiber and the receiving optical fiber are divided into multiple pairs, and detection is sequentially carried out along a small section of infusion tube under the control of the scanning circuit (the scanning frequency is far greater than the moving speed of bubbles), so that the bubbles can be prevented from being missed to be detected, and the detection is absolutely not lost.
6. The infusion pump is further provided with the optical fiber type bubble sensor for reference corresponding to the optical fiber type bubble sensor for detection, and by the arrangement of the reference device, the problem that the existing infusion pump is easily influenced by factors such as the light transmittance of an infusion tube and an infused liquid, the change of a light source, dust and a photosensitive element to the temperature change is solved, the precision of bubble detection is greatly improved, and the possibility that the bubbles enter a human body to cause gas embolism to cause breathing discomfort is reduced.
7. This disclosure flow sensor, utilize the pressure differential that the pressure sensor at sampling capillary both ends detected to carry out flow detection according to the Poiseue's law, can realize completely that the liquid medicine flow to the infusion in-process detects, compare in current flow sensor, its detection precision is higher, can more effectual closed-loop control who realizes the infusion volume, moreover, this disclosure small flow sensor only need capillary and pressure sensor's cooperation can realize the flow detection of high accuracy, its cost is far less than current product, specific high use and spreading value.
Drawings
Fig. 1 is a schematic view of the overall structure of a high-precision analgesic pump provided in embodiment 1 of the present disclosure.
Fig. 2 is a schematic structural diagram of a micro flow regulator provided in embodiment 1 of the present disclosure.
Fig. 3 is a schematic structural diagram of a water pressure box provided in embodiment 1 of the present disclosure.
Fig. 4 is a schematic structural diagram of an optical fiber bubble sensor provided in embodiment 1 of the present disclosure.
Fig. 5 is a block diagram of a control circuit provided in embodiment 1 of the present disclosure.
1-a flow stopping clip; 2. a filler neck protective cap; 2-1, a puncture outfit; 2-2, a medicine adding port tee joint; 3. an infusion bag; 3-1, an infusion bag infusion port; 4. a water pressure box; 5. a manual three-way reversing valve; 5-1, a concave port of a manual three-way valve; 5-2, a concave opening of the manual three-way reversing valve; 6. fixing the clamping piece; 7. a miniature speed reduction motor; 8. a micro flow regulator; 9. a nut slider; 10. a screw; 11. a square slide bar; 12. a movable clamping piece; 13. a waterway connecting pipe; 14. a first pressure sensor; 15, tee joint; 16. sampling a capillary tube; 17. a second pressure sensor; 18. a manual four-way reversing valve; 18-1, a concave port of the manual four-way reversing valve; 19. a water pump housing; 20. a piston; 21. a spring; 22. an optical fiber type bubble sensor for detection; 23. emitting the optical fiber bundle; 24. a scanning circuit; 25. a light emitting diode; 26. a fiber-optic bubble sensor for reference; 27. a self-holding electromagnet; 28. a transfusion tube; 29. a receiving optical fiber bundle for detection; 30. a photodiode for detection; 31. a photodiode for reference; 32. a convex lens; 33. a reference receiving fiber bundle; 34. a filter; 35. a port fitting; 36. a first silicone tube; 37. a silicone tube middle connecting piece; 38. a first Hall limit switch; 38-1 and a second Hall limit switch; 39. a second silicone tube; 40. a limiting magnet; 41. a first silicone tube connector; 41-1 and a second silicone tube connecting piece; 42. a liquid outlet hole; 43. a hollow round bar; 44. a damping iron rod; 45 damping magnet 46, concave card slot; 47. a box cover sealing ring; 48. sealing the buckle; 49. an exhaust valve; 50. a hydraulic box cover; 51. a sealing ring at the outer outlet of the infusion bag; 51-1 and an outer outlet of the infusion bag; 52. a hydraulic cartridge housing; 53. a water inlet male joint; 54. a hidden box cover; 55. a fiber optic bubble sensor cassette housing; 56. a micro deceleration electric drive circuit; 57. a self-holding electromagnet drive circuit; 58. a microcontroller; 59. a sound drive circuit; 60. a first amplifying circuit; 61. a second amplifying circuit; 62. a temperature sensor; 63. a display module; 64. and a key module.
Detailed Description
It should be noted that the following detailed description is exemplary and is intended to provide further explanation of the disclosure. Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure belongs.
It is noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of example embodiments according to the present disclosure. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, and it should be understood that when the terms "comprises" and/or "comprising" are used in this specification, they specify the presence of stated features, steps, operations, devices, components, and/or combinations thereof, unless the context clearly indicates otherwise.
The embodiments and features of the embodiments in the present disclosure may be combined with each other without conflict.
Example 1:
the embodiment 1 of the present disclosure provides a high-precision analgesia pump, as shown in fig. 1 to 5, including an infusion tube 28, a microcontroller 58, a water pump, a flow rate detection device and a micro flow rate regulator 8, where the water pump includes a water pump housing 19, a piston 20 and a spring 21, the piston 20 and the water pump housing 19 form a first chamber, the spring 21 and one end of the piston 20 far away from the first chamber are fixedly connected, and the spring 21 is in a compressed state;
the flow detection device comprises a sampling capillary tube 16 and pressure sensors of the same type arranged at two ends of the sampling capillary tube, namely a first pressure sensor 17 and a second pressure sensor 14, wherein the first pressure sensor 6 and the second pressure sensor 8 are respectively in communication connection with a microcontroller 58 through a first amplification circuit 60 and a second amplification circuit 61, one end of the sampling capillary tube 16 is connected with the water outlet end of a first cavity through a manual four-way reversing valve 18, the manual four-way reversing valve 18 comprises a manual four-way reversing valve concave port 18-1, the first pressure sensor 17 and the second pressure sensor 14 are both in communication connection with the microcontroller 58, and when liquid (such as water) passes through the sampling capillary tube 16, the microcontroller performs infusion flow detection by utilizing the pressure difference of the liquid at two ends of the sampling capillary tube according to the Poiseup's law;
the micro flow regulator 8 comprises a micro speed reducing motor 7, a screw rod 10, a nut slide block 9, a square slide rod 11, a fixed clamping piece 6, a movable clamping piece 12, a first silicone tube 36, a silicone tube middle connecting piece 37, a hollow round rod 43 and a second silicone tube 39, one end of the first silicone tube 36 is connected with a first silicone tube connecting piece 41 which is fixed by a fixing piece 6, the second silicone tube connecting piece is connected with the water outlet end of the sampling capillary tube 16 through a waterway connecting tube 13 and a tee joint 15, one end of the hollow round rod 43 is open and passes through the first silicone tube connecting piece 41 to be connected with a waterway connecting tube, the other end of the hollow round rod 43 is closed and penetrates through the second silicone tube 39 to reach the silicone tube middle connecting piece 37, a liquid outlet 42 is formed in the hollow round rod 43, and the outer diameter of the hollow round rod 43 is smaller than the inner diameter of the first silicone tube 36;
the other end of the first silicone tube 36 is connected with one end of a second silicone tube 39 through a silicone tube middle connecting piece 37, the other end of the second silicone tube 39 is connected with a second silicone tube connecting piece 41-1, the silicone tube middle connecting piece 37 is connected with the square slide bar 11 through a hanging piece and can slide along the square slide bar 11, the second silicone tube connecting piece 41-1 is fixedly connected with a movable clamping piece 12, the movable clamping piece 12 is fixedly connected with a nut slide block 9 and can move along a screw rod 10 and the square slide bar 11, the water outlet end of the first silicone rubber connecting piece is connected with the water pressure box 4 through a manual three-way reversing valve 5, a manual three-way valve concave port 5-1 is connected with a water pressure box convex connector 53 through a water path connecting pipe, and the manual three-way valve concave port 5-2 is used for filling water into the water pressure box 4; concave clamping grooves 46 are formed in the first silicon rubber connecting piece 41 and the second silicon rubber connecting piece 41-1 and used for clamping the fixed clamping piece and the movable clamping piece.
The infusion bag is arranged in the water pressure box 4, the water pressure box 4 is filled with water, and the output end of the infusion bag 3 is connected with the infusion tube 28;
the microcontroller 58 controls the micro speed reduction motor 7 to rotate the screw rod moving nut slide block 9 to drive the moving clamping part 12 through the micro speed reduction electric drive circuit 56 in real time according to the detected transfusion flow value, further drives the first silicone tube 36 and the second silicone tube 39 to stretch and retract so as to change the diameter and the length of the tubes, controls the extension of the silicone tube to increase the flow resistance and reduce the flow when the flow is greater than a given value, and otherwise controls the shortening of the silicone tube to reduce the flow resistance and increase the flow when the flow is less than the given value, and adjusts the stretching and retracting of the silicone tube to stabilize the flow on the given value.
The first silicone tube 36 and the second silicone tube 39 are made of the same material, and the wall thickness of the second silicone tube 39 is larger than that of the first silicone tube 36.
A damping iron rod 44 is fixed on one side of the silicone tube intermediate connecting piece far away from the slide rod, the silicone tube intermediate connecting piece further comprises a damping magnet 45 opposite to the damping iron rod 44, the damping magnet 45 is fixedly connected with the self-holding electromagnet 27, and the self-holding electromagnet 27 controls the distance between the damping magnet 45 and the damping iron rod 44 through a self-holding electromagnet driving circuit 57 according to the instruction of the microcontroller 58, so that the action of the silicone tube intermediate connecting piece 37 is controlled.
The nut slider is fixed with a magnet 40, a first Hall limit switch 38 and a second Hall limit switch 38-1 are arranged at a preset interval along the direction of the square sliding rod 11, and when the magnet is close to the first Hall limit switch 38 or the second Hall limit switch 38-1, the microcontroller 58 controls the micro speed reduction motor 7 to stop.
Be equipped with detection on the position that is close to syringe needle port joint on transfer line 28 and use optic fibre formula bubble sensor 22, detection is with optic fibre formula bubble sensor 22 including setting up the many emission optic fibre bundles 23 that set up side by side along the transfer line direction of transfer line one side and set up at the transfer line opposite side with the detection of emission optic fibre with receive optic fibre bundle 29, the detection sets up with the light-emitting port of emission optic fibre bundle 23 and first photodiode 30 relatively, just be equipped with lens 32 between the light-emitting port of emission optic fibre bundle 23 and first photodiode 30, first photodiode 30 and microcontroller 58 communication connection.
Still including setting up the reference optical fiber formula bubble sensor 26 after the position of detecting with optical fiber formula bubble sensor on the transfer line, the optic fibre setting in the reference optical fiber formula bubble sensor 26 is the exact same with the optical fiber formula bubble sensor 22 for detection, the emitting fiber sharing emitting diode 25 in reference optical fiber formula bubble sensor 26 and the detecting with optical fiber formula bubble sensor 22 is as the light source, microcontroller 58 passes through scanning circuit 25 control emitting diode 25 and goes out, the reference of reference optical fiber formula bubble sensor 26 is with receiving optic fibre bundle 33 and the relative setting of second photodiode 31, be equipped with lens 32 between reference receiving optic fibre bundle 33 and the second photodiode 31.
The light emitted from the light emitting diode 25 is divided into two paths by the emission optical fiber bundle 23, one path is a standard light path, the standard light intensity is determined by the reference optical fiber type bubble sensor 26 without bubbles and is irradiated onto the reference photodiode 31 through the reference reception optical fiber bundle 33, and the other path is a light path to be measured and is irradiated onto the detection photodiode 30 through the detection reception optical fiber bundle 29 through the infusion tube. When no bubble exists, the light intensity received by the photosensitive diode 30 for detection and the light intensity received by the photosensitive diode 31 for reference are the same, because the bridge output formed by the photosensitive diode and the resistor with the same light intensity is zero, when the bubble exists, the bubble enables the light intensity received by the photosensitive diode for detection to change, the photocurrent changes (the impedance changes), and the photocurrent of the photosensitive diode for reference does not change (the impedance does not change), the bridge outputs signals, thereby detecting the information of the bubble.
Before infusion, medical staff firstly exhausts air in an infusion tube 28, at the moment, no air bubble (namely, standard light intensity) exists in the reference optical fiber type air bubble sensor 26, if the air bubble occurs in the infusion process, the air bubble firstly passes through the detection optical fiber type air bubble sensor 22, the light intensity received by the detection photosensitive diode is changed by the air bubble, the light current is changed (impedance is changed), and the bridge outputs signals, so that the air bubble information is detected.
The microcontroller 58 is also connected to the key module 64, the display module 63 and the sound driving circuit 59, and is used for implementing manual input of control commands, real-time display of relevant parameters and alarm in case of abnormal conditions.
The microcontroller 58 is further connected with a temperature sensor 62, the temperature sensor 62 is used for detecting the temperature in real time, and the microcontroller 58 determines a corresponding viscosity value according to the detected temperature value.
The optical fiber bubble sensor for detection 22 and the optical fiber bubble sensor for reference 26 are provided in an optical fiber bubble sensor cassette case 55, and the optical fiber bubble sensor cassette case 55 is covered by a cassette cover 54.
The second photodiode 31 is in communication connection with a microcontroller 58, and the microcontroller 58 is configured to determine whether bubbles are generated according to the contrast between the brightness of the first photodiode 30 and the brightness of the second photodiode 31.
The water pressure box 4 comprises a water pressure box shell 52, a box cover 50 is arranged at the top of the water pressure box, a box cover sealing ring 47 is arranged on the box cover 50, the box cover 50 is fixedly connected with the shell through a sealing buckle 48, an air outlet is formed in the box cover 50, the opening and closing of the air outlet are controlled through an air exhaust valve 49, a water inlet convex connector 53 and an infusion bag outer connector 51-1 are arranged on the water pressure box shell 52, and the infusion bag outer connector 51-1 is sealed through an infusion bag outer outlet sealing ring 51.
The infusion tube is communicated with an infusion bag infusion port 3-1 through a puncture outfit 2-1, the puncture outfit 2-1 is connected with the infusion tube 28 through a medicine feeding port tee joint 2-2, a liquid feeding port is arranged on the medicine feeding port tee joint 2-2, a liquid feeding port protective cap 2 is arranged on the liquid feeding port, a flow stopping clamp 1 is arranged at a position, close to the medicine feeding port tee joint 2-2, on the infusion tube 28, a port connector 35 is arranged at the end of the infusion tube, and a filter 34 is arranged on a tube section between the port connector 35 and the reference optical fiber type bubble sensor 26.
The flow detection method of the high-precision analgesia pump in the embodiment specifically comprises the following steps: when liquid flows in the sampling capillary tube, the pressure sensors at the two ends of the sampling capillary tube convert corresponding pressure signals into electric signals and transmit the electric signals to the microcontroller, and the microcontroller obtains the flow Q of the liquid in the sampling capillary tube according to the Poiseul's law as follows:
Q＝K(p2-p1)/η
wherein (p)2-p1) Is the pressure difference between two ends of the sampling capillary, eta is the viscosity coefficient of the liquid, K is the geometric constant of the sampling capillary, and K is pi R4L8L, R is the inner radius of the sampling capillary, L is the sampling capillaryThe length of the tube is pi, the circumference ratio is pi, the viscosity eta of the reference liquid is obtained by looking up the table, and then the flow of the liquid flowing in the sampling capillary tube is obtained by calculation.
The flow sensor part is composed of a sensing element and a conversion element, wherein the sensing element is a sampling capillary tube, the conversion element is a pressure sensor, the sampling capillary tube plays a role in sensing liquid flow, and the two pressure sensors play a role in converting corresponding signals into electric signals.
Assuming a flow rate Q of 2mL/h per hour (2mL/h), a sampling capillary radius R of 0.12mm, a sampling capillary length L of 100mm, and a viscosity η of 1.009 x 10-3Pa.S (temperature 20 ℃ C.).
From the Poisea law, the pressure difference across the sampling capillary is found to be:
P2-P1＝8ηLQ/πR4＝690(Pa)＝0.69(KPa)
a pressure sensor with a little higher sensitivity can meet the detection of 0.69KPa (but not high price).
For example, the pressure sensor model MPX2010DP has a sensitivity of 2.5mv/KPa, 0.69KPa 2.5mv/KPa 1.725mv (no flow sensor with a flow rate of 1ml/h has been found, and if the sensor is expensive).
The flow regulating method of the high-precision analgesia pump in the embodiment has the following control principle:
when the fluid makes laminar flow motion in the circular tube, the flow rate is as follows according to Poiseul's law: q ═ Δ p/RfWhere Q is the flow, Δ P is the pressure difference, RfIs the flow resistance (the magnitude of which is determined by the viscosity of the fluid, the length and radius of the tube, i.e. Rf＝8ηL/(πr4) It can be seen that the formula is similar to ohm's law in electricity (I ═ U/R).
The length of the first silica gel tube is 40mm, the inner diameter of the first silica gel tube is 0.8mm, the length of the hollow rod is 60mm, the outer diameter of the hollow rod is 0.6mm, the length of the second silica gel tube is 30mm, the inner diameter of the second silica gel tube is 0.4mm, and when the total length of the silica gel tubes is 110mm, the flow can be adjusted to be 0.5ml/h (the requirement of adjusting the infusion amount to be 2ml/h is met).
The specific flow regulating method comprises the following steps:
the flow is detected in real time by the sampling capillary tube 16, namely, the pressure at two ends of the sampling capillary tube 14 is detected in real time by the first pressure sensor 14 and the second pressure sensor 17 and fed back to the microcontroller 58, the microcontroller compares a feedback value with a given value and controls the micro speed reducing motor 7 to rotate the screw rod 10 and move the nut slider 9 to drive the moving clamp 12 in real time, the silicone tube is driven to stretch and contract to change the geometric parameters (diameter and length changes) of the tube, namely, the flow resistance is changed, when the flow is greater than the given value, the silicone tube is controlled to extend to increase the flow resistance (diameter is reduced and length is increased) to reduce the flow, otherwise, when the flow is less than the given value, the silicone tube is controlled to shorten to reduce the flow resistance (diameter is increased and length is reduced) to increase the flow, and the flow Q is stabilized on the given value by adjusting the stretching and contracting of the silicone tube;
the conventional method is to adjust the flow by adjusting the opening size by moving a valve core, and the method can generate large flow change even for a small stroke (change by a few tenths of millimeters) of a small flow.
The specific principle is as follows: when the fluid makes laminar flow motion in the circular tube, the flow rate is as follows according to Poiseul's law: q ═ Δ P/R, where Q is the flow, Δ P is the pressure differential, and R is the flow resistance (the magnitude of which is determined by the viscosity of the fluid, the length and radius of the tube, i.e., ═ 8 η L/(π R ═ R4). It can be seen that the formula is similar to ohm's law in electricity (I ═ U/R), i.e. it is similar to regulating current by adjusting resistance.
The principle for realizing coarse adjustment and fine adjustment is that the wall thickness of the second silicone tube is larger than that of the first silicone tube, namely the elastic coefficient of the second silicone tube is larger than that of the first silicone tube, when the silicone tube stretches, such as when the magnet is not in contact with the damping rod, the acting force applied to the silicone tube is the same (equivalent to the series connection of two springs), so that the movement amount of the first silicone tube is larger than that of the second silicone rubber (the acting force applied to the silicone tube is the same when the silicone tube is in series connection, and the movement amount with large elastic coefficient is small), when the damping magnet is in contact with the damping iron rod, the movement amount of the second silicone tube is larger than that of the first silicone rubber by the damping action (the acting force applied to the first silicone tube is reduced), and the damping iron rod and the damping magnet are arranged to realize coarse adjustment and fine adjustment of the two silicone rubbers by using a set of screw nut slider.
The method comprises the following specific steps:
the wall thickness of the second silicone tube 39 is larger than that of the first silicone tube 36, when the flow is larger than a given value, the microcontroller 58 controls the first silicone tube 36 and the second silicone tube 39 to extend to increase the flow resistance and reduce the flow, at the moment, the change range of the diameter and the length of the first silicone tube 36 is far larger than that of the second silicone tube 39, coarse flow adjustment is achieved, at the moment, the diameter is mainly adjusted, the flow resistance is inversely proportional to the diameter of the first silicone tube by a power of 4, the microcontroller 58 controls the damping iron rod located in the middle connecting piece 37 of the silicone tube to be in contact with the damping magnet, damping is further generated on the middle connecting piece of the silicone tube, at the moment, only the diameter and the length of the second silicone tube 39 are adjusted, at the moment, the length is mainly adjusted, the flow resistance is proportional to the length of the silicone tube, fine flow adjustment is achieved, the coarse adjustment range can be larger, the fine adjustment can be more accurate, and the coarse adjustment and the fine adjustment can be matched with each other to improve the accuracy.
The microcontroller 58 controls the damping iron rod 44 to be in incomplete contact with the damping magnet 45 and to have a certain gap, and the damping iron rod 44 can do certain damping movement along the damping magnet 45, so that the flow regulation mainly based on fine adjustment is realized.
Adding water into the water pressing device, which specifically comprises the following steps:
the manual four-way reversing valve 18 is screwed to be communicated with the concave port 18-1, water is injected into the water pressure pipe through the port by using an injector, and the reversing valve 18 is screwed to be disconnected with the concave port 18-1 (and the water pressure pipe is communicated with the sampling capillary 16) after the water is injected.
The operation of adding the liquid medicine into the infusion bag specifically comprises the following steps:
sleeving a sealing ring 51 on an infusion bag infusion port 3-1 of an infusion bag 3, putting the infusion bag infusion port into a water pressure box, penetrating the infusion bag infusion port 3-1 out of the water pressure box through an infusion bag outer outlet 51-1, connecting an infusion tube 28 to the infusion bag infusion port 3-1 of the infusion bag 3 (connecting the infusion tube through a puncture outfit 2-1), opening a liquid filling port protective cap 2, injecting liquid medicine into the infusion bag 3 through a liquid filling port by using an injector (after the liquid medicine is added, screwing the liquid filling port protective cap 2 up and screwing), and finishing the liquid medicine adding operation.
The operation of adding water to the water adding pressure box specifically comprises the following steps:
the water pressure box 4 is connected with the concave interface 5-1 of the hand-operated directional valve 5, the directional valve is screwed to be communicated with the concave interface 5-2 (the air release valve 49 is opened at the same time), water is injected into the water pressure box through the port by an injector, the directional valve 5 is screwed to be disconnected with the concave interface 5-2 (the air release valve 49 is closed at the same time) after the water is fully filled, and the water adding operation is finished.
Finally, the liquid stopping clamp 1 is opened, and infusion is carried out by a preset infusion program.
The above description is only a preferred embodiment of the present disclosure and is not intended to limit the present disclosure, and various modifications and changes may be made to the present disclosure by those skilled in the art. Any modification, equivalent replacement, improvement and the like made within the spirit and principle of the present disclosure should be included in the protection scope of the present disclosure.
Claims (9)
1. A high-precision analgesia pump is characterized by comprising an infusion tube, a microcontroller, a water pump, a flow detection device and a flow adjusting device; the water pump is used for providing liquid with pressure to the flow detection device, and the flow detection device is used for detecting the flow of the liquid in real time and transmitting the flow to the microcontroller;
the flow regulating device comprises a miniature speed reducing motor, a screw rod, a nut slider, a sliding rod, a fixed clamping piece, a movable clamping piece, a first silicone tube, a silicone tube middle connecting piece, a hollow round rod and a second silicone tube, wherein one end of the first silicone tube is connected with the first silicone tube connecting piece, the first silicone tube connecting piece is fixed through the fixed clamping piece, the second silicone tube connecting piece is connected with the water outlet end of the sampling capillary tube through a waterway connecting tube, one end of the hollow round rod is opened and penetrates through the first silicone tube connecting piece to be connected with the waterway connecting tube, the other end of the hollow round rod is closed and penetrates through the second silicone tube to penetrate into the silicone tube middle connecting piece, a liquid outlet hole is formed in the hollow round rod, and the outer diameter of the hollow round rod is smaller than the inner diameter of the first silicone tube;
the other end of the first silicone tube is connected with one end of a second silicone tube through a silicone tube middle connecting piece, the other end of the second silicone tube is connected with a second silicone tube connecting piece, the silicone tube middle connecting piece is connected with a sliding rod through a hanging connecting piece and can slide along the sliding rod, the second silicone tube connecting piece is fixedly connected with a movable clamping piece, the movable clamping piece is fixedly connected with a nut sliding block and can move along a screw rod and the sliding rod, the water outlet end of the second silicone tube connecting piece is connected with a water pressure box, an infusion bag is arranged in the water pressure box, the water pressure box is filled with water, and the output port of the infusion bag is connected with an infusion tube;
an optical fiber type bubble sensor for detection is arranged on the infusion tube at a position close to the joint of the needle head port;
the microcontroller controls the micro speed reducing motor to rotate the screw rod and move the nut slide block to drive the movable clamping piece in real time according to the detected transfusion flow value, further drives the first silica gel tube and the second silica gel tube to stretch and contract to change the diameter and the length of the tubes, controls the extension of the silica gel tube to increase the flow resistance and reduce the flow when the flow is greater than a given value, otherwise controls the shortening of the silica gel tube to reduce the flow resistance and increase the flow when the flow is less than the given value, and adjusts the stretching of the silica gel tube to stabilize the flow on the given value;
still including setting up the reference after the position of detecting with optic fibre formula bubble sensor on the transfer line and using optic fibre formula bubble sensor, optic fibre setting in the reference with optic fibre formula bubble sensor is the exact same with the detection with optic fibre formula bubble sensor, optic fibre formula bubble sensor for the reference and the interior transmission optic fibre of detecting with optic fibre formula bubble sensor share a light source, the reference sets up with reference photodiode relatively with optic fibre formula bubble sensor for the reference, photodiode and microcontroller communication connection for the reference, microcontroller is used for judging whether there is the bubble to produce according to the output of bridge with the electric bridge that photodiode and reference are constituteed, according to the output of electric bridge.
2. The pump of claim 1, wherein the first and second silicone tubes are made of the same material, and the second silicone tube has a greater wall thickness than the first silicone tube.
3. The high precision analgesic pump of claim 1, wherein the water pump comprises a water pump housing, a piston, and a spring, wherein the piston and the water pump housing form a first chamber, and the spring is fixedly connected to an end of the piston away from the first chamber.
4. The pump as claimed in claim 1, wherein the flow detection device comprises a sampling capillary tube and pressure sensors of the same type disposed at two ends of the sampling capillary tube, one end of the sampling capillary tube is connected to the water outlet of the water pump, the pressure sensors are in communication with the microcontroller, and when the liquid passes through the sampling capillary tube, the microcontroller performs the infusion flow detection by using the pressure difference of the liquid at two ends of the sampling capillary tube according to Poiseul's law.
5. The pump as claimed in claim 1, wherein a damping iron rod is fixed to the silicone tube intermediate connector at a side away from the slide rod, and a damping magnet is fixed to the silicone tube intermediate connector opposite to the damping iron rod, the damping magnet is fixedly connected to a self-holding electromagnet, and the self-holding electromagnet controls a distance between the damping magnet and the damping iron rod according to a command from the microcontroller, thereby controlling the operation of the silicone tube intermediate connector.
6. The pump as claimed in claim 1, wherein the nut slider has a magnet fixed thereon, and a first hall limit switch and a second hall limit switch are provided at a predetermined interval in the direction of the slider, and the micro-controller controls the micro-reduction motor to stop when the magnet is close to the first hall limit switch or close to the second hall limit switch.
7. The pump as claimed in claim 1, wherein the optical fiber bubble sensor for detection comprises a plurality of emitting optical fibers arranged side by side along the direction of the infusion tube on one side of the infusion tube and a receiving optical fiber arranged on the other side of the infusion tube and opposite to the emitting optical fibers, wherein the light outlet of the receiving optical fiber is opposite to the photodiode for detection, the photodiode for detection is in communication connection with the microcontroller, and the microcontroller determines whether bubbles are generated according to the brightness change of the photodiode for detection.
8. The high-precision analgesia pump according to claim 1, wherein the water pressure box comprises a water pressure box shell, a box cover is arranged at the top of the water pressure box, a box cover sealing ring is arranged on the box cover, the box cover is fixedly connected with the shell through a sealing buckle, an exhaust port is arranged on the box cover, the opening and the closing of the exhaust port are controlled through an exhaust valve, a convex water inlet and an infusion bag external port are arranged on the water pressure box shell, and the infusion bag external port is sealed through an infusion bag external outlet sealing ring.
9. A method for operating a high-precision analgesic pump, wherein, with the high-precision analgesic pump as claimed in any one of claims 1-8, when there is a liquid flowing in the sampling capillary, the pressure sensors at both ends of the sampling capillary convert the corresponding pressure signals into electric signals and transmit the electric signals to the microcontroller, and the microcontroller obtains the flow Q of the liquid in the sampling capillary according to poisson's law as:
Q=K(p2-p1)/η
wherein (p)2-p1) Is the pressure difference between two ends of the sampling capillary, eta is the viscosity coefficient of the liquid, K is the geometric constant of the sampling capillary, and K = pi R4And 8L, wherein R is the inner radius of the sampling capillary, L is the length of the sampling capillary, and pi is the circumferential ratio, the viscosity eta of the reference liquid is obtained by looking up the table, and the flow rate of the liquid flowing in the sampling capillary is further calculated.
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| CN1441682A (en) * | 2000-05-19 | 2003-09-10 | 普莱姆泰克公司 | Device for controlling flow of fluid |
| US20090054867A1 (en) * | 2002-02-18 | 2009-02-26 | Peter Gravesen | Device for Administering of Medication in Fluid Form |
| CN101785887A (en) * | 2009-01-22 | 2010-07-28 | 深圳市深科医疗器械技术开发有限公司 | Automatic infusion pump |
| CN107802918A (en) * | 2017-11-16 | 2018-03-16 | 北京来普惠康医学技术有限公司 | A kind of dynamic action is in the transfusion control method and control system of decoction soft bag |
| CN209028051U (en) * | 2018-10-31 | 2019-06-25 | 冠礼控制科技（上海）有限公司 | A kind of titrator sample bubble detection system |
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|---|---|---|---|---|
| CN1441682A (en) * | 2000-05-19 | 2003-09-10 | 普莱姆泰克公司 | Device for controlling flow of fluid |
| US20090054867A1 (en) * | 2002-02-18 | 2009-02-26 | Peter Gravesen | Device for Administering of Medication in Fluid Form |
| CN101785887A (en) * | 2009-01-22 | 2010-07-28 | 深圳市深科医疗器械技术开发有限公司 | Automatic infusion pump |
| CN107802918A (en) * | 2017-11-16 | 2018-03-16 | 北京来普惠康医学技术有限公司 | A kind of dynamic action is in the transfusion control method and control system of decoction soft bag |
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